Artificial tympanic membrane devices and uses

ABSTRACT

This disclosure features artificial tympanic membrane graft devices and two-component bilayer graft devices that include a scaffold having a plurality of ribs made of a first material and a plurality of spaces between the ribs filled or made with the first material, a different, second material, a combination of the first and a second materials, or a combination of a second material and one or more other different materials. The bilayer graft devices have two components or layers. One component, e.g., the underlay graft device, can include a projection, and the second component, e.g., the overlay graft device, can include an opening that corresponds to the projection (or vice versa) so that the opening and the projection can secure the two layers together in a “lock and key” manner. This disclosure also features methods of making, using, and implanting the three-dimensional artificial tympanic membrane and bilayer graft devices.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/559,582, filed Sep. 19, 2017, which is a § 371 U.S. National PhaseApplication of International Application No. PCT/US2016/023482, filed onMar. 21, 2017, and claims the benefit of U.S. Application Ser. No.62/247,268, filed on Oct. 28, 2015, U.S. Application Ser. No.62/245,827, filed on Oct. 23, 2015 and U.S. Application Ser. No.62/136,097, filed on Mar. 20, 2015. The entire contents of the foregoingare incorporated herein by reference.

FIELD OF THE INVENTION

The present document relates to artificial grafts.

BACKGROUND OF THE INVENTION

Three-dimensional (3D) printing is a type of additive manufacturing inwhich a desired 3D shape or object is built up from an available supplyof material. In some cases, the material is initially a solid that istemporarily melted, a liquid that is solidified, or a powder that issolidified during the manufacturing process. Examples of 3D printingtechniques include stereolithography, in which a photo-responsive resinis hardened with a laser; fused deposition modeling (FDM), in which asolid material is melted, printed, and fused to surrounding materialwhen solidified; filamentary extrusion/direct ink writing, in which theink is extruded from a nozzle head via pressure and the resultant objectcan be cured or sintered; and granular material binding, in which a bedof granular material is bound, often with heat or a fluid binder. Other3D additive manufacturing methods include Fused Filament Fabrication(FFF), Stereolithography (SLA), Digital Light Processing (DLP),Electron-beam melting (EBM), Selective laser melting (SLM), Selectiveheat sintering (SHS), Selective laser sintering (SLS), Direct metallaser sintering (DMLS), Laminated object manufacturing (LOM), andElectron Beam Freeform Fabrication (EBF3).

A tympanic membrane graft is an implant or transplant used in theperformance of tympanoplasty, the surgical operation performed toreconstruct and/or repair a patient's tympanic membrane. Tympanoplastyprocedures may also involve reconstruction of the middle ear ossicles asthey are in continuity with the tympanic membrane. Tympanic membranegrafts typically consist of autologous temporalis fascia, perichondrium,cartilage, and/or skin grafts. Tympanoplasty is often referred to asmyringoplasy when only the tympanic membrane is addressed surgically.

SUMMARY

Artificial tympanic membrane devices can be constructed by preparing,for example, by 3D printing, a scaffold of ribs, and subsequently orsimultaneously infilling open spaces or voids between the ribs with thesame or different materials to form a membrane. Together, the scaffoldand membrane form the artificial tympanic membrane device, which canthen be used as a surgical graft to be implanted into subjects, e.g.,human patients, with, for example, chronic otitis media—a persistentinflammation of the middle ear resulting from poor ventilation throughthe Eustachian tube, perforations in a patient's tympanic membrane,scarred tympanic membranes with poor mobility, or blast injuries in themilitary or civilian populations, chronic retraction of the tympanicmembrane, as well as other clinical etiologies.

The new graft devices also can be used as in vitro tools to studytympanic membrane properties by analyzing particular structural featuresof the membranes and then recreating these features independentlythrough a 3D printing platform.

Bilayer tympanic membrane graft devices, e.g., interlocking bilayergraft devices, can be prepared using similar techniques to thesingle-component artificial tympanic membrane devices, and can be usedto repair tympanic membrane perforations, e.g., subtotal perforations.These two-component bilayer graft devices include an underlay graftdevice designed to adhere to the underside of the tympanic membranefacing the middle ear, and an overlay graft device that is secured ontop of the tympanic membrane facing the external ear canal. One of thetwo graft components, e.g., the underlay graft device, includes aprojection, e.g., an interlocking projection, designed and configured tofit into and extend through the perforation and interlock with anopening in the second component, e.g., the overlay graft device, tosecure the bilayer graft device such that the tympanic membranesurrounding the perforation and surrounding cuff of healthy TM tissue issandwiched between the two components (layers) of the graft device topromote wound repair and ensure proper biological environmental milieu.The opening in the overlay device and the projection in the underlaydevice can fit together in a so-called “lock and key” design.

In some embodiments, the two graft components can be secured by a tissueor other biocompatible adhesive, e.g., a fibrin glue, or a tether orstitch to hold the two components together. In these embodiments, theremay be no projection, or each component can include a projection thatpasses through the perforation to meet and contact the projection fromthe other component (thus these projections are typically shorter andsimpler in configuration than in the lock and key approach). Inaddition, even in the lock and key approach, an adhesive canadditionally be used.

In one aspect, this disclosure features artificial tympanic membranegraft devices that include a scaffold that includes a plurality of ribsmade of a first material or combination of materials, and a plurality ofopen spaces or voids between the ribs filled or made with the firstmaterial or combination of materials, a different, second material, acombination of the first and a second materials, or a combination of asecond material and one or more other different materials, e.g., to forma thin artificial membrane between the ribs. In certain implementations,these graft devices can be used to form an underlay graft device, e.g.,by connecting to a surface of the artificial tympanic membrane device aprojection configured to fit through a tympanic membrane perforation, oran overlay graft device having an opening configured to fit over andlock into a corresponding projection of an underlay graft device.

Implementations of the new devices can include any combination, one,all, or none of the following features. At least some ribs of thescaffold can be formed in circular shapes and at least some ribs of thescaffold can form a radial pattern. At least some ribs of the scaffoldcan be formed in a hub and spoke arrangement. At least some ribs of thescaffold can be formed in a group of concentric geometric shape, e.g., aflat circular shape. The artificial tympanic membranes can be designedto form a circular conical shape or some other 3D shape, e.g., a portionof a cone. In various embodiments, the first material, e.g., a scaffoldor rib material, can include one or more of polydimethylsiloxane (PDMS),hyaluronic acid (HA), poly(glycolic acid) (PGA), poly(lactic-co-glycolic acid) (PLGA), polylactic acid (PLA), polyestercarbonate urethane urea (PECUU), poly octamethylene maleate anhydridecitrate (POMaC), poly(glycerol sebacate) (PGS),poly(octanediol-co-citrate) (POC), polyurethane, collagen (e.g., typeIII collagen), fibrin, extracellular matrix, nylon, silk,poliglecaprone, and elastin. Hydrogels can also be included, e.g., inmixtures with other scaffold/rib materials already listed above.

The second material, e.g., an infill material, can include one or moreof the first materials and/or one or more hydrogels and/or one or moreother materials. Some examples of infill materials that can be used inthe methods described herein include, but are not limited to, collagen,e.g., type III collagen, extracellular matrix, hydrogels, e.g., fibrinhydrogel, titanium dioxide, cellulose, gelatin, agarose, alginate,poly(N-isopropylacrylamide), hyaluronic acid, poly(vinyl alcohol) (PVA),poly (acrylic acid) (PAA), polycaprolactone,poly(3-hydroxybuterate-co-3-hydroxyvalerate, pluronic PLA, PGA,transglutaminase, PLGA, PDMS, poliglecaprone, polyester carbonateurethane urea (PECUU), poly octamethylene maleate anhydride citrate(POMaC), poly(glycerol sebacate) (PGS), poly(octanediol-co-citrate)(POC), polyurethane, and a mixture of collagen and fibrin. The secondmaterial can thus include mixtures of two or more of these materials,e.g., collagen and fibrin or collagen, fibrin, and a hydrogel thatsupports the growth of cells. These infill materials can also be used asthe scaffold/rib materials, and vice versa.

The devices can further include one or more of a cellular adhesionand/or a cell invasion-inducing material, e.g., growth factors. Thedevices can further include one or more cells, e.g., fibroblasts,chondrocytes, keratinocytes, stem cells, progenitor cells, andepithelial cells. The cells can be harvested from the patient or fromdifferent sources, e.g., a transplant from another subject or fromcultured cell lines. The growth factors can include a fibroblast growthfactor (FGF), vascular endothelial growth factor (VEGF),platelet-derived growth factor (PDGF), and a keratinocyte growth factor(KGF). These growth factors can be included either directly in theentire infill or preferentially patterned during the 3D printing processto replicate native growth factor gradients or polarize sides of thetympanic membrane (TM) to promote and “tune” ingrowth of different celltypes. The devices can further include one or more drug elutingmaterials.

In various embodiments, the devices can have a diameter of 0.5 to 12millimeters, e.g., 1, 2, 3, 5, 7, 9, 10, or 11 mm. The devices can havea diameter based on a specific patient, e.g., a human patient. Thedevices can have a thickness of 10 to 750 microns, e.g., 25, 50, 75,100, 125, 150, 175, 200, 250, 300, 400, 500, 600, or 750 microns. Insome embodiments the devices are impermeable to air while in otherembodiments they can be permeable to air. The devices can also bedesigned to be permeable to one or more drugs or other agents includingsmall molecules, biologics, steroids, and antibiotics.

In some embodiments, the devices can include an ossicular connector onone surface of the tympanic membrane graft. The ossicular connector canbe formed as an artificial umbo, malleus, or stapes and take the shapeof one of an umbo, malleus, or stapes, or of a ring, a hinge, loop,archway, or a ball or socket, or some combination thereof. For example,such ossicular connectors can be secured to a surface of an artificialtympanic membrane graft devices, e.g., an underlay graft device. Invarious embodiments, the connector can connect to a remnant ossicularchain in the patient's middle ear or to an ossicular prosthesisimplanted in the middle ear before or at the same time as the tympanicmembrane graft(s) are implanted.

In another aspect, the disclosure features methods of implanting theartificial tympanic membrane devices as described herein into a patientto heal or augment a damaged tympanic membrane or to replace a missingtympanic membrane or portion thereof, e.g., to repair a perforation. Thedisclosure also features the use of any of the devices described hereinto heal, augment, or replace a damaged or missing tympanic membrane. Themethods include accessing the damaged or missing tympanic membrane;obtaining an appropriately sized and configured artificial tympanicmembrane device; and securing the artificial tympanic membrane device toseal the damaged portion of the tympanic membrane or replacing themissing tympanic membrane or missing portion thereof. For example, onecan repair a tympanic membrane perforation by inserting a compressed orrolled underlay graft device through the perforation and allowing theunderlay graft device to unfurl and adhere to the underside of thetympanic membrane facing the middle ear, and then connecting an overlaygraft device to a projection of the underlay device, at least a portionof which extends through the perforation to secure the bilayer graftdevice with the tympanic membrane surrounding the perforation sandwichedbetween the two layers of the graft device. An insertion device can alsobe used to place the underlay and/or the overlay graft.

In some embodiments, the projection can be secured to the overlaydevice, or the overlay and underlay devices can be connected ormanufactured in one piece before implantation into the ear (e.g., in theshape of a “dumbbell” in which a narrow central connecting portion ofthe dumbbell passes through the perforation in the tympanic membrane tosecure two wider flat portions on either side of the tympanic membrane).

The disclosure also features methods of fabricating one or more of theartificial tympanic membrane graft devices and the interlocking bilayergrafts devices described herein. These methods include forming ascaffold including a plurality of ribs using a first material, orcombination of materials, and defining one or more open spaces betweenthe ribs; and forming a thin membrane in the open spaces between theribs using the first material or combination of materials, a different,second material, a combination of the first and a second materials, or acombination of the second material and one or more other differentmaterials. Thereafter or during constructing of the first component,e.g., for an underlay graft device, a specifically shaped projection isconstructed in place or is later secured to the graft device. At least aportion of the projection is configured to fit through the perforationto be repaired. For example, the projection can be T-shaped,button-shaped, or ball-shaped. While an external profile of theprojection can be designed and constructed to correspond precisely tothe tympanic membrane perforation, this is not required as long as theprojection, or a portion of the projection, fits through theperforation. For the second component, e.g., the overlay graft devices,each is constructed or cut after construction to include an opening thatcorresponds to the external shape of the projection on the underlaygraft device.

In another aspect, the disclosure features new bilayer tympanic membranedevices that include or consist of a pair of artificial tympanicmembrane devices described herein. In these bilayer device, a firstcomponent of the pair of artificial tympanic membrane devices furthercomprises a projection, and wherein a second component of the pair ofartificial tympanic membrane devices further comprises an openingconfigured to enable insertion of the projection, wherein the firstcomponent and the second component can be secured to each other. In someimplementations, the opening and the projection can include or consistof a lock and key configuration, a socket and ball configuration, or anopening and hinge configuration.

The disclosure also features methods of repairing a tympanic membraneperforation and the use of the new bilayer tympanic membrane devices torepair such perforations. The methods include obtaining a bilayertympanic membrane device as described herein; inserting the firstcomponent as an underlay graft device through the perforation andsecuring a surface of the underlay device to the tympanic membrane suchthat the projection protrudes through the perforation; applying thesecond component as an overlay device over the perforation such that theprojection protrudes through the opening of the overlay device andextends beyond a surface of the overlay device; and moving one or bothof the overlay device and the projection or underlay device with respectto each other such that a portion of the projection is securely fit ontoa surface of the overlay device to lock the underlay and overlay devicestogether, sandwiching the tympanic membrane and perforation betweenthem.

In these methods, a top surface of the underlay device can be adhered tothe inner surface of the tympanic membrane by capillary action oradhesion, or a tissue adhesive, such as a fibrin glue. The methods canbe performed in a clinical setting with or without local analgesia, andwithout sedation or general anesthesia. In some implementations, themethods are performed in an operating room with sedation or anesthesia.

Implementations of the new methods can include any combination, one,all, or none of the following features. The new methods of fabricatingthe scaffold can include printing the scaffold with a three-dimensional(3D) printer and filling the one or more voids between the ribs byfilling with a second material. The 3D printer can include a nozzle forextruding the first material, wherein the nozzle can have an opening of500 μm or less in diameter, e.g., 10 to 500, 10, 20, 30, 40, 50, 75,100, 150, 200, 250, 300, 350, 400, or 450 μm or less in diameter.Printing the scaffold can include printing the scaffold onto a substratethat includes one or more of glass, poloxamer, polytetrafluoroethylene(PTFE), and metal foil, e.g., aluminum foil. Infilling the voids of thescaffold with the second material can include removing the scaffold froma substrate of the 3D printer; filling a well with the second materialin a liquid form; placing the scaffold in the well with the secondmaterial; and curing the scaffold and infilled second material tosolidify the second material. Curing the scaffold and infilled secondmaterial to solidify the second material includes incubating thescaffold and infilled second material in deionized water at 37° Celsius.

In some implementations, the scaffolds can be prepared using, forexample, using polydimethylsiloxane (PDMS), hyaluronic acid (HA),poly(glycolic acid) (PGA), poly (lactic-co-glycolic acid) (PLGA),polylactic acid (PLA), polyester carbonate urethane urea (PECUU), polyoctamethylene maleate anhydride citrate (POMaC), poly(glycerol sebacate)(PGS), poly(octanediol-co-citrate) (POC), polyurethane, elastin,collagen, e.g., spun collagen, fibrin, nylon, silk, poliglecaprone, andpolymers of any one or more of these materials, e.g., hyaluronic acidpolymers. The infilled second material can be any of these materialsand/or can be a hydrogel, such as a bovine fibrin hydrogel.

The systems and processes described here can be used to provide a numberof advantages. The new artificial tympanic membrane graft devices andinterlocking bilayer graft devices can be acoustically tuned to mimic orimprove upon the acoustic properties of perforated or otherwise damagedtympanic membranes, e.g., of a specific patient, or of a group ofpatients. In addition, the new artificial tympanic membrane graftdevices can be designed to resist perforation and retraction, and toprovide a robust attachment to the ossicular chain or directly to thefootplate into the inner ear. These grafts can be designed to beimpermeable to air or liquids or permeable to air but not liquids,and/or permeable to small molecules and/or biologics or other specificagents. In some embodiments, the graft's geometry can be designed basedon the anatomical features and deficits of the particular patient forwhom they are intended. The grafts can be made of materials that haveequivalent or greater mechanical strength than a natural tympanicmembrane or natural, tissue-based membrane graft, which can reduce thechance of perforations and/or retraction. The materials can bedimensionally stable, which can help avoid retraction, and provide forsecure attachment to the ossicular chain. 3D printing technology is usedto recapitulate the conical shape of a native TM or design a patch tomatch the curvature of the patient's TM. Conical shapes can be creatingthrough the use of supporting molds or sacrificial materials, such aspluronic inks.

The devices can be designed with or without an ossicular connectorcomponent which, incorporated into the tympanic membrane, would allowdirect attachment of the tympanic membrane to the ossicular chain ordirectly to the footplate of the inner ear to ensure robust coupling ofacoustic energy from the tympanic membrane to the inner ear. Thetympanic membrane grafts described herein can facilitate the delivery ofdrugs and/or air to the middle ear, thus improving and expediting woundhealing, can improved conductive hearing, can decrease the need forre-operation for revision surgery, and can be customized and/orpersonalized to provide grafts based on a patient's size of defect andacoustic needs.

Use of the new tympanic membrane grafts can avoid the need for a secondoperation for hearing reconstruction. These grafts can increase the easeof surgical manipulation and can be easily handled due to beingformulated to the appropriate size preoperatively. In addition,absorbable or non-absorbable materials can be used and selected based onpatient-specific criteria and criteria of the surgery being performed.The new interlocking bilayer graft devices can be inserted into apatient's ear to repair a tympanic membrane perforation using eitherstandard surgical tools to manipulate the two portions of the device orusing a specialized insertion tool having the shape of a cylindricaltube that enables the graft to be easily deployed through theperforation into the middle ear. In addition, the new methods can oftenbe conducted in a doctor's office without the need for generalanesthesia and thus can, in many situations, avoid the need for surgeryand hospitalization.

Unless otherwise defined, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention belongs. Although methods and materialssimilar or equivalent to those described herein can be used in thepractice or testing of the present invention, suitable methods andmaterials are described below. All publications, patent applications,patents, and other references mentioned herein are incorporated byreference in their entirety. In case of conflict, the presentspecification, including definitions, will control. In addition, thematerials, methods, and examples are illustrative only and not intendedto be limiting.

Other features and advantages of the invention will be apparent from thefollowing detailed description, and from the claims.

DESCRIPTION OF DRAWINGS

FIG. 1A is a schematic view of a human tympanic membrane.

FIG. 1B is a top view of an example of a tympanic membrane graft device.

FIGS. 2A and 2B are views of examples of scaffolds of a tympanicmembrane graft including a ring connector (as shown in FIG. 2B).

FIG. 2C is a photographic representation of an example of an ossicularconnector on the surface of a tympanic membrane graft device scaffoldthat has a single arch ring connector design for attachment to theossicular chain.

FIG. 2D is a photographic representation of an example of an ossicularconnector on the surface of a tympanic membrane graft device scaffoldthat has a double arch ring connector design for attachment to theossicular chain.

FIGS. 2E-A to 2E-D are photographic representations of tympanic membranepatch graft scaffolds of various designs.

FIG. 3A is a view of examples of scaffolds of varying sizes andgeometries.

FIG. 3B-A to 3B-C are a series of images of tympanic membrane scaffoldscomposed of PDMS, PLA, and PCL filaments/ribs, respectively, with 8C(C=circumferential fiber/rib structure)/8R (R+radial fiber/ribstructure) and 16C/16R filamentary architectures. The TMs in the firstcolumn of each box have a total diameter of 25 mm. The next two columnsshow higher magnification images, 50× with a scale bar of 1 mm and 100×with a scale bar of 500 respectively.

FIG. 3B-D is an image of a representative printed scaffold highlightingthe key design features.

FIGS. 3C-A and 3C-B are photographic representations of a graft devicewith a fractal fiber/rib structure pattern, with and without a borderrib structure, respectively.

FIGS. 4A and 4B are schematic figures of an underlay graft device and anoverlay graft device, respectively.

FIGS. 5A and 5B are examples of a scaffold of a tympanic membranegrafts.

FIGS. 6A and 6B are photographic representations of an underlay graftdevice and an overlay graft device, respectively, showing a scaffold andinfill material.

FIG. 6C is a photographic representation of a combined bilayer graftdevice, in which the projection of the underlay of FIG. 6A is pulledthrough the opening in the overlay device of FIG. 6B, and the overlaydevice is rotated to wedge the top or “arms” of the T-shaped projectionover the surface of the overlay device, thereby securing the twotogether.

FIGS. 7A and 7B together form a flow chart of an example of a processfor creating tympanic membrane grafts.

FIGS. 8A, 8B, and 8C are schematic representations that show an exampleof a tympanic membrane graft scaffold being printed by a 3D printer.FIG. 8D shows the scaffold being filled with infill material.

FIG. 8E is a schematic illustration of how a doctor can place one of thetympanic membrane graft devices into the ear canal and onto the tympanicmembrane.

FIGS. 9A-9D are schematic representations of the use of the bilayergraft devices described herein to seal a tympanic membrane perforation.

FIGS. 10A-10D are a series of schematic diagrams showing a fiber/ribarrangement template (FIG. 10A), a tympanic membrane perforation imagedonto the fiber template (FIG. 10B), a customized tympanic membrane patchgraft or bilayer graft device in which the central region includes ribsdesigned to match the ribs in the location of the perforation (FIG.10C), and placement of the device over the perforation to effect repair(FIG. 10D).

FIGS. 11A-1 to 11A-4 are photographic representations of a PDMS scaffold(11A-1), a collagen/fibrin infilled scaffold (11A-2), a magnified imageof FIG. 11A-2 , showing cells growing on the device (11A-3), and afurther magnification of FIG. 11A-3 (11A-4).

FIGS. 11B-1 and 11B-2 are three-dimensional plots that show cells thathave grown on the surface of scaffolds and infill material during invitro cell studies.

FIGS. 12A-A to 12A-G; 12B-1 to 12B-8, 12C-1A to 12C-1D, 12C-2A to12C-2D, 12D-1A to 12D-1B, and 12D-2A to 12D-2B are photographicrepresentations of acoustic testing devices and graphicalrepresentations of data of acoustic properties of printed tympanicmembranes collected from acoustic testing.

FIGS. 13A-13B are photographic representations that show a trimmedtympanic membrane graft implanted to repair a perforation in thetympanic membrane of a sheep.

FIGS. 14A-14C are photographic representations of the use of a tympanicmembrane patch graft to seal a TM perforation in a chinchilla model.

FIGS. 15A-D are a series of graphs that show results of laser Dopplervibrometry (“LDV”) measurements on graft devices as described herein.

FIG. 16A-C are photographic representations of tympanic membrane graftshaving conical shapes.

Like reference symbols in the various drawings indicate like elements

DETAILED DESCRIPTION

Artificial tympanic membrane devices and interlocking bilayer graftdevices are described, along with some processes for manufacturing suchmembrane devices, uses of such membrane devices, and the results oftests performed on such membrane devices.

To specifically address partial tympanic membrane perforations (whichrepresent the majority of perforations seen in clinical practice), wehave devised a bilayer, interlocking TM graft to facilitate perforationrepair. The graft may potentially be used in the clinic setting, therebyavoiding general anesthesia and surgery-related morbidity, such as frompost-auricular or transcanal soft tissue incisions. Alternatively, thegraft may be used in an operating room setting with sedation oranesthesia, if required in specific situations. Placed through the earcanal, the new graft devices provide the advantages of surgicaltympanoplasty without the need for an operation. The bilayer designallows for a combination underlay and overlay graft approach usingscaffold fiber arrangements with favorable acoustic and resilientmechanical properties. Unlike “patch” approaches to TM repair, this“sandwich” bilayer design grafts components to both the outer ear andinner ear surfaces of the TM, providing an ideal environment forcellular migration and proliferation and healing of the TM after injury.3D printing can be used to produce the new key/lock devices to ensurestability of the graft, even in the face of positive or negative middleear pressure. However, other types of features may be used instead ofthe lock and key. For example, a ball and socket, hinge, tether, stitch,and/or adhesive may be used.

Tympanic Membrane Graft Devices

Artificial tympanic membrane graft devices, or simply “grafts,” asdescribed herein are designed to be acoustically tuned (i.e., modifiedto the extent that the acoustic properties are adjusted for best soundconduction in a specific patient), resistant to perforation andretraction, and to provide a robust attachment to the ossicular chain.The artificial tympanic membrane grafts can have a scaffold, e.g., in a2D or 3D layer, made of ribs, with voids between the ribs. An infillmaterial, e.g., a hydrogel, is typically used to fill the voids and tocreate a solid, optionally semipermeable, artificial tympanic membranegraft. These artificial tympanic membrane grafts can be used as implantsto repair, replace, or patch a patient's tympanic membrane. Similarly,the interlocking bilayer grafts can be used to seal tympanic membraneperforations.

In some embodiments, the artificial grafts, e.g., an interlockingbilayer grafts, are implanted without any living cells present, butincludes agents that will induce cells from the patient's ear canal tomigrate and colonize the graft within a time period of several weeks tomonths. In other embodiments, the scaffold and infill materials are usedas a substrate for living cells, e.g., harvested from the patient orfrom other subjects, to cover or be integrated within all or part of thescaffold and/or infill materials.

FIG. 1A is a prior art schematic view of a human tympanic membrane.Inspiration for the circular and radial rib structure of the 3D printedtympanic membranes was derived from the fiber arrangement in the naturaltympanic membrane. Circular and radial fibers along with a malleusregion were traced using a Visual G-code program. The drawing wasconverted into a G-code program that was 3D printed via filamentaryextrusion of SE1700 polydimethylsiloxane (PDMS).

In some embodiments the artificial tympanic membrane grafts and the twolayers and projection of the bilayer grafts can be manufactured by first“printing” the scaffold using a 3D printer that dispenses abiocompatible “ink.” Once solidified and removed from the 3D printer'sprinting surface, the scaffold can be submerged in a curable liquid.This liquid can fill the voids between ribs of the scaffold, and then becured to form a solid membrane between the ribs of the scaffold. Oncecured, the artificial tympanic membrane graft can be used intympanoplasty and/or myringoplasty operations for the reconstruction ofa patient's tympanic membrane. In addition, the bilayer grafts can beused to simply and effectively repair tympanic membrane perforations.

In other embodiments the artificial tympanic membrane grafts and bilayergrafts can be manufactured by printing the scaffold and the infillmaterial simultaneously or serially using a 3D printer that dispensesone or more types of biocompatible inks. The ribs and infill materialmay consist of two different printed materials, or in some circumstancesmay consist of different patterns of the same material. Once manufactureis complete, the graft is removed from the 3D printer's printing surfaceand cured by one or more methods, which may include for example, heatcuring, curing by UV light, carbon dioxide or other gas, pressure, orcooling. This material may have other useful properties, such as beingabsorbable or non-absorbable, permeable or non-permeable, drug eluting,cellularized, etc.

FIG. 1B is a top view of a schematic of an artificial tympanic membranegraft 100. The shape of the tympanic membrane graft 100 may be generallycircular, with a center that may be elevated or flat to create anoverall shape that is, or that approaches, a circular, flat, or conicalconstruct. The tympanic membrane graft 100 includes ribs 102 and voids104 filled with an infill material. This arrangement of ribs allows fora biomimetic architecture that may allow the 3D printed tympanicmembranes to have similar or improved acoustic and mechanic propertiesto the native tympanic membrane.

The overall size and shape of the tympanic membrane graft 100 may beselected based on the patient for which the tympanic membrane graft 100is created. For example, for an adult human, the tympanic membrane graft100 may be created with a diameter on the order of a few millimeters.For example, the diameter of the tympanic membrane graft 100 can beabout 0.5, 1, 2, 3, 5, 8, 10, 12, 14, 16, 17, 18, or 19 millimeters, ormore or less as is technologically and physiologically appropriate. Forexample, smaller sizes may be appropriate to patch a tympanic membranewhile larger sizes may be appropriate when used to completely replace atympanic membrane.

The size and shape of the bilayer grafts will depend on the size of theoverall tympanic membrane of the patient, but more importantly based onthe size of the perforation. Both the underlay graft and the overlaygraft should be at least about 1 to 2 mm larger in size than thegreatest dimension of the perforation. In addition, the projection onthe underlay (or overlay) can be a host of different shapes and sizes tofacilitate placement.

Scaffolds

FIGS. 2A and 2B are views of examples of scaffolds of tympanic membranegrafts. The views shown were created from a photograph of the scaffoldtaken before all of the infill material was added to fill voids of thescaffold.

The scaffold includes many ribs. Some of the ribs of the scaffold areformed in circular, or nearly circular, shapes. In addition, some of theribs of the scaffold are formed in straight, or nearly straight shapesarranged in a radial pattern. Alternatively, some of the ribs of thescaffold may be described as forming a hub and spoke arrangement, whilesome other ribs of the scaffold are formed in a group of concentricgeometric shapes.

Between the ribs of the scaffold are voids. The voids are areas withoutany material of the scaffold. Infill materials are used to fill thevoids, as will be discussed below. In some embodiments, the samematerial as used for the ribs, or a different material, can also be usedto 3D print a thin sheet of material to fill the voids.

The cross-sectional shape of the ribs may be any technologicallyappropriate shape, including but not limited to circular, rectangular(e.g., square), triangular, or irregular. The diameter or thickness (atthe widest point) of the ribs may be on the order of tens to hundreds ofmicrons. For example, the thickness of the individual ribs may be from 5to 50 microns up to 500 to 800 microns, e.g., 10 to 100 microns, 100 to500 microns, or 5, 10, 25, 50, 75, 100, 125, 150, 175, 200, 225, 250,275, 300, 325, 350, 375, 400, 425, 450, 475, 500, 550, 600, 650, 700750, or 800 microns, or more or less as is technologically andphysiologically appropriate. The ribs can also be shaped to form anossicular connector to enable connection of the tympanic membrane graftto the malleus, incus, or stapes, or to a remnant of one of theossicles, or to a commercially available existing prosthesis, ordirectly to the inner ear, e.g., to the footplate of the oval window.The connector may replace the ossicular chain in entirety or onecomponent of it. This connector can be made of the same or a differentmaterial, e.g., hydroxyapatite, titanium, or nitinol, from the materialused for the rest of the scaffold. As shown in FIGS. 2B to 2D, theconnector may take the shape of a ball and socket, snap, hinge, circularaperture, or different connecting configuration that would attach anintegrated component from the tympanic membrane to the native orsynthetic ossicle(s).

FIG. 2A shows an example of a scaffold with additional material beyondthe circumference of the scaffold. The additional material may be thesame or different material from the graft scaffold and infill, and mayserve as means to secure the graft for in vitro testing, or for mountingin the eardrum to the ear canal in live surgery. The central region isthe scaffold, surrounded by radially extending ribs. Voids between theribs can be filled with infill material.

FIG. 2B shows an example of a scaffold with additional material tofunction as a connector region to attach the graft to ossicularprostheses. A printed scaffold with a connector loop enables anossicular prosthesis to be crimped onto the tympanic membrane graft tocreate a solid connection between the tympanic membrane graft and theossicular chain or oval window. FIG. 2C is a photo of an example of anossicular connector on the surface of a tympanic membrane graft devicescaffold that has a single arch ring connector design for attachment tothe ossicular chain. FIG. 2D is a photo of an example of an ossicularconnector on the surface of a tympanic membrane graft device scaffoldthat has a double arch ring connector design for attachment to theossicular chain.

FIGS. 2E-A to 2E-D are photographic representations of tympanic membranepatch graft scaffolds of various designs referred to herein as tunablearc patches that include arc fibers (A), radial fibers (R) and a borderregion around the outside of the device. These patches can be usedindividually or as part of the bilayer devices described herein. Each ofthese elements of the device can be designed (i.e., “tuned”) to meetspecific needs of a particular patient.

FIG. 3A is a view of several examples of different scaffolds 300-314 ofvarying sizes and geometries. As shown, scaffolds can be created withvarying overall diameters, including diameters ranging from 8 mm to 14mm. However, larger and/or smaller diameters are possible, depending ona particular patient's needs. Each of the scaffolds 300-314 includeribs, and each of the scaffolds 300-314 include a different number ofribs and voids arranged in different configurations. FIGS. 3B-A to 3B-Cshow other scaffolds with differing numbers and arrangements of radialfibers (R) circumferential fibers (C) and a border region fibermanufactured polydimethylsiloxane (PDMS), hyaluronic acid (HA),poly(glycolic acid) (PGA), poly (lactic-co-glycolic acid) (PLGA),polylactic acid (PLA), polyester carbonate urethane urea (PECUU), polyoctamethylene maleate anhydride citrate (POMaC), poly(glycerol sebacate)(PGS), poly(octanediol-co-citrate) (POC), and/or polyurethane. FIG. 3B-Dshows the basic format.

The underlay graft devices and overlay graft devices can be manufacturedin the range of about 2 to 8 mm, or larger, as required to repair aparticular perforation. These devices are typically about 100 to 300microns thick, e.g., about 150 to 250 microns, e.g., 200 microns, thick.

In addition to those shown, other arrangements of ribs are possible,including non-regular or regular geometric arrangements. As each of thescaffolds 300-314 has a different number and arrangement of ribs, eachof the scaffolds 300-314 has voids of different sizes, shapes, andaggregate sizes. That is, the sum total volume of voids between any twoscaffolds (including those not shown) need not be the same. As will bedescribed later, these tympanic membrane grafts can be designed for usefor different patients, including different patients of differentspecies. As such, the size of the scaffold, and thus the final tympanicmembrane graft, can be selected based on the patient that will receivethe graft.

Scaffolds can be created from any technologically appropriate material.For example, the material used may be selected to be biocompatible,capable of being manufactured to the size at which the scaffold isdesigned, and possessing the necessary mechanical properties tofacilitate the transmission of vibrations to the patient once implanted.Some examples of materials that can be used in the methods describedherein include, but are not limited to, polydimethylsiloxane (PDMS)(which is non-absorbable by the body), hyaluronic acid (HA),poly(glycolic acid) (PGA), poly (lactic-co-glycolic acid) (PLGA),polylactic acid (PLA) (which is absorbable), poly(glycerol sebacate)(PGS) (e.g., REGENEREZ®—a tunable, bioresorbable elastomer made of PGSwith elastomeric properties), polyurethane, polyvinyl alcohol (PVA),nylon, silk, poliglecaprone, polycaprolactone (PCL) (which is absorbableby the body), polyester carbonate urethane urea (PECUU), polyoctamethylene maleate anhydride citrate (POMaC),poly(octanediol-co-citrate) (POC), collagen, fibrin, and elastin.

The scaffold can also be plasma treated to enhance adhesion of theinfill materials and enhance cellular binding capabilities. Plasmatreatment cleans the samples and also puts hydrophilic groups on thesurfaces so that biologic materials, such as collagen and fibrin, canadhere more readily. Other treatment of scaffolds may includeapplication of substances that improve cellular adhesion includingoxidation, treatment with poly-D-lysine, 3-aminopropyl triethoxysilane(APTES), and cross-linking with glutaraldehyde (GA). In some cases, thescaffold may be drug eluting. For example, drugs such as β-fibroblastgrowth factor (FGF-β), ciprofloxacin, and dexamethasone can be deliveredusing the new graft devices.

These same types of scaffolds can be used to create the new bilayergraft devices, with some modifications to produce a projection on theunderlay graft device and a corresponding opening or aperture in theoverlay graft device. The projection is created from the same ordifferent scaffold material as the ribs, and can be manufactured at thesame time the ribs are produced or can be manufactured separately andthen secured to the surface of the scaffold for the underlay device.Similarly, the opening in the overlay device can be created while thescaffold is being laid down, or can be cut out of the overlay deviceonce the scaffold is completed, similar to one of the transmembranegraft devices described herein.

In general, the fiber and/or rib arrangements can contain 2 to 8 or morearrangements to create a mechanically stiffened and resilient structure.For example, 4 circular rib structures, 4 radial rib structures to 8circular rib structures, and 8 radial rib structures. These arrangementscan also form other patterns such as hexagonal or fractal designs tofacilitate cell growth, e.g., as shown in FIGS. 3C-A and 3C-B. Suchfractal designs can include repeating patterns, branching ribs, orsnowflake-like patterns.

The dimensions of the bilayer graft devices can be in the range of 2-8mm in diameter×200 microns in thickness for both the overlay andunderlay graft devices, and the projection (“key”) on the underlaydevice can be about 200 microns×1 mm.

As shown in FIG. 4A, the underlay device 350 can have a scaffold 360 anda projection 370, which can have the shape of a shallow “T” in which theshort base of the “T” is part of or is secured to the scaffold material360, e.g., to the ribs, e.g., in the center of a circular underlay graftdevice 250, and extends upwards a distance that is about the same sizeor slightly larger than the thickness of the overlay graft device 380(shown in FIG. 4B). The top of the “T” extends perpendicularly from thebase, and the length of the top is about the same size or slightlysmaller than the largest dimension of the opening in the overlay device.In general, to accommodate the “T”-shaped projection, as shown in FIG.4B, the opening 390 in the overlay device 380 is generally rectangular,e.g., square, in shape and has the same general dimensions as a top viewof the top of the “T,” so that the top of the T-shaped projection 370can easily pass through the opening 380, but can pass over a top surfaceof the overlay graft device 380 when the overlay is turned with respectto the underlay deice 350, to secure the overlay device to the underlaydevice in a so-called “lock and key” manner. Of course, the projection370 can have other shapes and the opening 390 can have a correspondingshape so that together the two function in a lock and key manner.

Other types of projections and “lock and “key” type mechanisms include abutton-shaped design, a hook and loop system, a ball and socket, adeployable umbrella, and a snap mechanism.

Infill Materials

One or more materials can be used to fill the voids of the scaffold of atympanic membrane graft device or bilayer graft device, and they can beadded to the scaffold using a variety of techniques. This infillmaterial or combination of materials can, for example, determine thepermeability or impermeability of the graft. The material may alsoinclude therapeutic or drug eluting materials (for the same or differentdrugs as used in or on the scaffold material), and can determine thesurface characteristics (e.g., texture) and other physicalcharacteristics of the graft. In some cases, the material used to infillthe voids is the same as, or includes, some or all of the material usedto create the scaffold. In addition, the infill materials can be addedto the scaffold in a separate step, or can be deposited in the same stepas the deposition of the ribs of the scaffold. For example, a 3D printercan be programmed to deposit the ribs and infill materials in one step,and the materials used for the scaffold and the infill material(membrane between the ribs) can be the same or different materials,because 3D printers can print one, two, or more different materials atthe same time.

FIGS. 5A and 5B are schematics of infilling a scaffold of a tympanicmembrane graft. In FIG. 5A, a semi-flat, cone-shaped scaffold 400 isremoved from a printing substrate by a pair of hemostats or forceps 402and is moved into a well containing infill material 404 shown in FIG.5B. In addition to hemostats or forceps 402, any sort of manipulatorscan be used, including, but not limited to, human operated manipulatorsand robotic manipulators working under direct human control or workingin an automated manner. In FIG. 5B, the infill material 404 has filledthe voids of the scaffold 400 and solidified.

FIG. 6A shows an underlay graft device 350 with a rectangular T-shapedprojection 370. FIG. 6B shows an overlay graft device 380 with ribs 382and clearly shows infill material 385 between the ribs. Opening 390 isclear of the infill material. As shown in FIG. 6C, the projection 370has been inserted or pulled through the opening 390 in the overlaydevice 380, and the overlay device has then been rotated so thatprojection 370 is securely fit over the opening 390 to secure theoverlay device to the underlay device.

The infill material 385, 404 may include any technologically appropriatematerial. For example, the material can be selected to be biocompatible,capable of filling voids in a scaffold, and possessing the necessarymechanical properties to facilitate the transmission of vibrations tothe patient once implanted. The material used can include some or all ofthe materials used in printing scaffolds. Some examples of infillmaterials that can be used in the methods described herein include, butare not limited to, collagen, e.g., type III collagen, extracellularmatrix, hydrogels, e.g., fibrin hydrogel, titanium dioxide, cellulose,gelatin, agarose, alginate, poly(N-isopropylacrylamide), hyaluronicacid, poly(vinyl alcohol), poly (acrylic acid), polycaprolactone,poly(3-hydroxybuterate-co-3-hydroxyvalerate, pluronic PLA, PGA,transglutaminase, PLGA, PDMS, poliglecaprone, polyester carbonateurethane urea (PECUU), poly octamethylene maleate anhydride citrate(POMaC), poly(glycerol sebacate), poly(octanediol-co-citrate) (POC),polyurethane, and a mixture of collagen and fibrin. These materials canbe used individually or in combinations of two of more differentmaterials.

In some embodiments, the infill material can include a cellular adhesionand invasion material. For example, such materials can be included toencourage a patient's tissues in the ear canal and/or middle ear toadhere to and grow over the tympanic membrane graft after implantation,or to cover the graft with cells before implantation. Examples of suchcellular adhesion and invasion material include, but are not limited to,growth factors such as one or more of a fibroblast growth factor (FGF),a vascular endothelial growth factor (VEGF), platelet-derived growthfactor (PDGF), transforming growth factor beta, interleukin-4, or otherfactors with similar biologic properties.

Additionally, the infill material can include, or be coated with in aseparate step, cellular materials. For example, such cellular materialscan include, but are not limited to, one or more of fibroblasts,chondrocytes, keratinocytes, and epithelial cells. These cells can beharvested from the patient who is to receive the implant or from arelative of the patient, or from a human subject unrelated to thepatient who is to receive the implant.

In addition, the infill material can include, or be coated with in aseparate step, one or more drug eluting materials. For example, suchdrug eluting materials can be included to deliver drugs to the tissue atthe graft site. Examples of such drug eluting materials include polymersthat allow tuned drug elution such as polyethylene vinyl acetate (PEVA),poly n-butyl methacrylate (PBMA), Polycaprolactone (PCL), Ethylene-vinylacetate (EVA), Polylactic acid (PLA),Poly(3-hydroxybutyrate-co-3-hydroxyvalerate (PHBV), phosphorycholine,and fluropolymer. Polymers with drugs can be printed, spray coatedand/or dip coated. In some cases, one to three or more layers can beused in the coating and the dose may therefore be tailored The drugs tobe eluted include, but are not limited to steroids, antibiotics,bisphosphonates, non-steroidal anti-inflammatory/immunomodulating drugs,e.g. biologics, TNF inhibitors, IL-6 inhibitor, IL-1 inhibitor, T cellmediators, antibodies that target inflammatory cells, e.g. B cells andcellular adhesion molecules, methotrexate, and cyclosporine.

Methods of Making the Artificial Tympanic Membrane Grafts

In general, creation or manufacture of a tympanic membrane graft deviceor bilayer graft device as described herein can include creation of oneor more scaffolds, followed by infilling the voids of the scaffold withan infill material. In some cases, the infill material begins as aliquid and is then set. Additional steps, or a different order of steps,may be used as technologically appropriate. For example, different stepscan be used to manufacture the graft (e.g., alternative order or typesof manufacturing), and additional steps may be performed once the graftis created (e.g., sanitizing, testing, packaging). For example, thefinal artificial tympanic membrane grafts can be sterilized usingradiation, including ultraviolet radiation, oxidization, or chemicalsterilization.

For example, any one or more of the following sterilants can be used,depending on the nature of the materials used for the scaffold andinfill material: ethylene oxide, ozone, bleach, glutaraldehyde and/orformaldehyde, phthalaldehyde, hydrogen peroxide, peracetic acid, orsilver. Some of these materials, e.g., silver, can also be incorporatedinto the scaffold and/or infill material during manufacture. Of course,if an artificial graft is to be covered with living cells, it would besterilized before the living cells are added to colonize the graft.

Described below is one possible process for manufacturing a tympanicmembrane graft. In this process, a scaffold is printed with a 3Dprinter, and the scaffold is submerged in a liquid curable infillmaterial after the scaffold is printed. In a different process, thescaffold and the infill material are both printed by the same or twodifferent 3D printers.

In yet another process, a scaffold is created by casting a firstmaterial in a first mold, and the scaffold voids are filled by 3Dprinting, use of a curable liquid material, or using a second castingwith a second material or combination of materials together with thescaffold in a second mold. Other methods are possible.

FIGS. 7A and 7B together form a flow chart diagram of an example of aprocess 500 for creating a tympanic membrane graft device or a bilayergraft device by printing a scaffold with a 3D printer, and the scaffoldis subsequently submerged in a liquid, curable infill material after thescaffold is printed. For clarity, process 500 is being described with aparticular set of machines serviced by autonomous material handlingrobots. However, different machines and different material handlingsystems, including human operators, may be used to perform the process500 or a similar process. Similarly, the example discusses creation of asingle tympanic membrane graft for clarity. However, some configurationsmay be used to create many tympanic membrane grafts at once, eitheridentical copies or different, e.g., personalized, copies havingdifferent properties.

A computer 502 is used to control the 3D printer and associatedequipment. Computer 502 can be a general-purpose computer such as adesktop or server computer. The computer 502 includes software to createmanufacturing instructions for other elements of the system shown inFIGS. 7A and 7B. Printer 504 is a 3D printer capable of printing one ormore scaffolds based on manufacturing instructions received from thecomputer 502. A curing oven and plasma treater 506 is a machine capableof curing a printed scaffold and/or applying a plasma treatment to theprinted scaffold. A hot plate and infill station 508 is a machine thatprovides a temperature controlled environment in which a scaffold can beinfilled. An incubator 510 is a machine that can hold a tympanicmembrane graft in a temperature controlled environment.

The computer 502 can receive parameters 512 for the manufacture of oneor more tympanic membrane grafts. For example, a user can enterparameters for a particular patient, including the patient's age,measurements made of the patient's ear canal and middle ear anatomy,medical imaging of the patient's anatomy, and/or a prescription for thepatient, etc. Additionally or alternatively, the user can enterparameters desired of the tympanic membrane graft itself. For example,the user may enter a desired diameter; number of layers, thickness;scaffold design; and/or drug, growth factors, and/or cellular adhesionand invasion materials. In some configurations, the computer 502 mayreceive some or all of the parameters from a network-connected datasource such as a purchasing or ordering computer, from electronicmedical records, or from another appropriate data source.

From the parameters, the computer 502 can generate a build plan 514 forthe desired tympanic membrane graft. The build plan 514 may include, forexample, machine instructions for machines involved in the tympanicmembrane graft's creation, instructions for a human operator, packagingand labeling information, etc.

In one example, to create instructions for the printer 504, a 3Dscaffold model may be selected from a library of 3D scaffold models. Theselected model may be picked based on, for example, fitting the size andshape specified in the parameters. Additionally or alternatively, a 3Dscaffold model may be modified, for example by scaling up or down,changing rib thickness, deepening or making more shallow the 3D conicalshape of the membrane, etc. The 3D model selected or created for thisbuild may then be converted into 3D printer instructions that, whenexecuted by the printer 504, cause the printer 504 to print the desiredscaffold.

In one example, to create instructions for the curing oven and plasmatreater 506, a curing time, curing temperature, and plasma treatmentparameters can be looked up or calculated based on, for example, thegeometry of the scaffold, the material used to print the scaffold, andother appropriate data.

In one example, to create instructions for the hot plate and fillstation 508, the computer 502 can select one or more materials for useas infill material. The infill materials may be picked based on, forexample, the size and geometry of the voids in the scaffold; desiredsurface characteristics; and/or desired drug, growth factors, and/orcellular adhesion and invasion material. The build plan may list thesematerial, along with, for example, volumetric measures or ratios of eachmaterial and an order for which they should be added to a well.

In one example, to create instructions for the incubator 510, thecomputer 502 can specify environmental factors needed to incubate atympanic membrane graft. For example, if the infill material is cured inan oven at 80° Celsius, the infill is crosslinked/gelled on a 37°Celsius hot plate. After a period of about 20 minutes, they aretransferred to a deionized water bath and placed in an incubator at 37°Celsius. In another example where the infill material is photo-curable,the build plan can include instructions to hold the tympanic membranegraft under an artificial light source at the proper temperature and fora specified length of time.

In one example, to create instructions for an automated materialhandling device, the computer 502 can specify an order of buildoperations and/or a time required for each build operations. The buildplan can include instructions to, for example, wait until a signal isreceived from the printer 504 before retrieving the scaffold from theprinter 504. The build plan can also include instructions to, forexample, wait a specified period of time before retrieving the tympanicmembrane graft from the curing station 508.

The printer 504, curing oven and plasma treater 506, hot plate andinfill station 508, and incubator 510 receive 516 the build plan. Forexample, the computer 502 can transmit, over a data network either wiredor wirelessly, the build plan, or a portion thereof according to thereceiving machine, to the other machines in the manufacturing system.Additionally or alternatively, information about the build plan may beoutput to a user device, for example, to allow a technician to approve,monitor, and/or participate in the manufacturing process.

The printer 504 can print 518 the scaffold. FIGS. 8A, 8B, and 8C show anexample of a tympanic membrane graft or bilayer graft scaffold beingprinted by a 3D printer. For example, the printer 504 generates a printjob from the build plans and begin printing the scaffold. In general,most printers 504 include a mechanism for creating a solid object fromgel, liquid or powder. In one example, a printer 504 can include anozzle for extruding build material onto a substrate. The printer 504controls the location of the nozzle in two dimension (e.g., x and y),and may control the elevation of the substrate in the third dimension(e.g., z). In some cases, the scaffold may be printed in a single layer,in which case the elevation of the substrate may be held constant duringthe printing process. In some cases, the scaffold may be printed inmultiple layers or printed on an uneven surface (e.g., cone) to obtain athin 3-dimensional shape, in which case the elevation of the substratemay be moved, e.g., lowered, from one layer to the next.

The nozzle of the printer 504 can be made of, for example, glass or ametal such as aluminum or stainless steel. The build material can beextruded through the opening of the nozzle, and may then form a layer ofthickness based on the size of the nozzle opening. Some example nozzlesmay have an opening on the order of microns in diameter. For example,the nozzle opening may be 2, 5, 10, 25, 75, 100, 120, 150, 175, 200,225, 250, 275, 300, 333, 475, 500, or 520 microns, a value in between,or more or less as is technologically appropriate.

The substrate that receives the printed scaffold can be made of amaterial appropriate for the build material. For example, the substratematerial can be selected based on the materials cohesion properties withthe build material so that the scaffold does not move as it is beingprinted, but can reliably be removed when the printing process iscompleted. Examples of substrate materials include, but are not limitedto, glass (e.g., pluronic-coated glass), poloxamer,polytetrafluoroethylene (PTFE), metal foil such as aluminum foil, orbiodegradable material, such as cellulose, for example. The substratecan be either flat or 3-dimensional in shape, allowing a thin constructto be created with depth (e.g. a conical membrane). The scaffold is thendeposited onto the substrate, e.g., as a series of circular ribstructures (as shown in FIGS. 8A and 8C) and/or radial rib structures(as shown in FIG. 8C).

The scaffold can be cured (step 520). For example, the material handlingsystem may move the scaffold to the curing oven and plasma treater 506,and send a command signal to the curing oven. The curing oven may thencure the scaffold for a time and at a temperature indicated by the buildplans 516.

The scaffold can be plasma treated (step 522). For example, the curingoven and plasma treater 506 can apply a plasma treatment specified bythe build plan 516. This plasma treatment may, for example clean thescaffold and/or alter the surface properties of the scaffold

After receiving the build plans, the hot plate and infill station 508prepares the identified infill material. For example, the hot plate andinfill station 508 may perform this operation while the scaffold isbeing printed, in response to an indication that the scaffold has beenprinted, or at a particular time.

The hot plate and infill station 508 can receive the infill material ormaterials in liquid form, for example from an automated or humanoperated source. If needed, the well station can also prepare anyenvironmental conditions necessary for the infilling as specified in thebuild plan or otherwise. For example, a fan in a vent hood may beactivated, air temperature or humidity may be controlled, and/orillumination may be increased or reduced.

If needed, other materials can be added. For example, any drug, growthfactors, and/or cellular adhesion and invasion material can be added.The order of addition and type of mixing, if any, is specified based onthe types of materials. For example, a non-volatile liquid may be addedfirst, followed by a volatile liquid so that the volatile liquid hasless time to evaporate. In another example, two or more materials may bemixed simultaneously.

The infill material is introduced to the scaffold 526. FIG. 8D shows anexample of a tympanic membrane graft scaffold receiving infill material.For example, an automated material handler, e.g., an automated robot, ora human operator, can remove the scaffold from the curing oven andplasma treater 506 and add the scaffold to the hot plate and infillstation 508. Here, the scaffold voids can be filled by the infillmaterial. In some cases, the infill material may be pipetted into thevoids of the scaffold, such as by a human or automated system. In somecases, submerging the scaffold in the infill material causes the voidsto be infilled. In some cases, the container holding the scaffold andinfill is agitated and/or the infill material is stirred to encouragethe infill material to fill the voids. In some operations to fill thevoids with the infill material, the scaffold may be flipped, and infillmaterial is added to both sides of the scaffold. In some operations,flipping is not needed.

After the infill material fills the voids of the scaffold, the materialhandling system can move the uncured tympanic membrane graft to theincubator 510. The incubator can incubate and store 526 the tympanicmembrane graft so that the tympanic membrane graft is a single, solidarticle. The configuration of the incubator 510 is designed based on theinfill material and/or other materials. For example, the incubator 510may include a temperature controlled water-bath, a humidity controlledair-hood, or any other technologically appropriate system for curing theinfill material. Once the device is completed, it can be implanted ontoor into a tympanic membrane (or replace a tympanic membrane), as shownschematically in FIG. 8E, in order to perform a tympanoplasty underlayand overlay. This represents the methods by which ear drum repair canoccur without need for general anesthesia or sedation. Of course, incertain situations, sedation or anesthesia may be required.

Graft Properties

As described previously, the tympanic graft's geometric properties arespecified in advance, e.g., based on the specific patient or group ofpatients who is or are to receive the graft. These properties may bedetermined in general (a particular size and shape for humans or othersubjects, e.g., a different size and shape for guinea pigs, lambs,chinchillas, sheep, dogs, cats, horses, monkeys, etc.), or in thespecific (based on measurements or imaging of a particular patient).

A tympanic membrane graft is generally designed to be acousticallytuned, resistant to perforation and retraction, and/or to provide arobust attachment point to the ossicular chain, such as directconnection to the malleus, incus, stapes, remnant of one of theseossicles, to a commercially available prosthesis, or in the case ofdisease, or completely replace the ossicular chain and connect directlyto the oval window of the cochlea. For example, the tympanic membranegraft may be made of materials that have greater mechanical strengththan a naturally occurring tympanic membrane or membrane graft, whichreduces the chance of perforations and/or retraction. In otherembodiments, the material may be stable in size and flexibility, whichcan help avoid retraction and provide for secure attachment to anycomponent of the ossicular chain or directly to the oval window.

By selection of scaffold material and/or infill material, a tympanicmembrane graft may be made to be impermeable to keep air, fluids such aswater, and debris from entering the middle ear. On the other hand, thetympanic membrane graft may be made of a material that is permeable toair, but to keep liquids out. This may allow, for example, air pressurein the middle ear to normalize with the pressure in the outer ear. Thismay be desirable for patients with poor ventilation through theEustachian tube. Additionally, the tympanic membrane graft may be madeof material that is also permeable to small molecules and/or biologics,termed “semipermeable membrane.” A semipermeable membrane may allow forthe transmission of, for example, steroids, antibiotics, inflammatorymediators, and or other medications through the tympanic membrane graftallowing drug delivery to the middle ear and/or inner ear.

Graft Uses and Methods of Implanting

The artificial tympanic membrane grafts described herein can be used forany appropriate tympanoplasty and/or myringoplasty operations for thereconstruction of a patient's tympanic membrane, including for use inboth human and non-human patients. The bilayer graft devices can be usedto simply and effectively seal tympanic membrane perforations as aminimally invasive method of tympanic membrane repair.

In many procedures, access to the tympanic membrane may be through theear canal itself, serving as a surgical portal, or an incision is madebehind or in front of the ear to access the tympanic membrane in need ofthe graft. These incisions may be one of an endaural incision or apostauricular incision. Once access to the patient's tympanic membraneis achieved, the native (diseased or remnant) tympanic membrane may beremoved and reconstructed in entirety (total tympanic membranereplacement) or in parts (patch/partial), or laid on top of an existingtympanic membrane with a defect (lateral myringoplasty), as a patch.

Once the artificial membrane graft is in place, the manubrium of themalleus (if present) is ensured to be contacting the surface of themembrane, drawing the membrane toward the tympanic cavity. Materials maybe used to ensure adhesion and attachment of the manubrium to theartificial membrane. Attachment of the artificial membrane to theossicles may cause the lateral surface of the membrane to become concaveand conical in shape. The depth of conical shape can be assed prior tograft placement and selected appropriately. The malleus can then beattached to the lowest or most depressed part of the concavity of themembrane (e.g., at the location of an artificial umbo serving as anossicular connector.)

There are variants possible, depending on the particular needs of apatient. For example, a tympanic membrane graft without an ossicularconnector can be placed over native ossicular chain, healing directly tothe manubrium of the malleus. A tympanic membrane with ossicularconnector that attaches to the malleus may be used if the malleus wasdiseased or partially foreshortened. The graft could connect to theremnant malleus via a socket for the remnant bone. This socket could bemade by preoperative imaging, or be created to a standard geometry.

A tympanic membrane with an ossicular connector that connects to theincus or remnant incus can also be used. In one configuration, a ring isincorporated into the tympanic membrane to allow a prosthetic to beattached to the ring and extend down to the incus. This connector wouldallow stable reconstruction of hearing. In other embodiments, a tympanicmembrane with an ossicular connector that connects to the stapes or astapes remnant can be used. This embodiment also takes the form a ringattached to the undersurface of the graft and would allow a prostheticto sit atop the stapes with a wire that hooks through the ring. Theconnector can be made of nitinol, which allows a laser to be used toactivate the “metal memory” and tighten the prosthesis down to thesurrounding structures and over the ring. Other configurations of theossicular connector are also possible and would include a ring, hinge,ball and socket joint or sliding joint.

The new bilayer graft devices are installed to repair a tympanicmembrane perforation in a multistep process as shown in FIGS. 9A to 9D.First, as shown in FIG. 9A, the perforation in the tympanic membrane isanalyzed to determine the size and shape. Next, as shown in FIG. 9B, theunderlay graft device is curled or rolled to reduce the overall size sothat it can be pushed through the perforation and unfurled once behindthe tympanic membrane so that the projection protrudes through theperforation. The top surface of the underlay device will adhere to theback surface of the tympanic membrane by capillary action or adhesion,or a tissue adhesive, such as a fibrin glue can be applied to thesurface of the underlay device, e.g., just prior to insertion.

Next, as shown in FIG. 9C, the overlay graft device is brought intoproximity of the underlay device. Next, the projection is pulled throughthe perforation and the opening in the overlay device. As shown in FIG.9D, the overlay device is then rotated about a central axis so that thetop of the projection, which generally does not move (or is held inplace so as not to move), is securely fit onto the surface of theoverlay device to lock the underlay and overlay devices together,sandwiching the tympanic membrane between them. FIG. 9D shows how therectangular projection is offset at a slight angle with respect to theopening in the overlay device.

FIGS. 10A-10D show another repair in which the ribs of the graft deviceare designed to match the structure of the tympanic membrane to berepaired. In particular, FIGS. 10A-10D show a fiber/rib arrangementtemplate based on images of the tympanic membrane to be repaired (FIG.10A), a tympanic membrane perforation imaged onto the fiber template(FIG. 10B), a customized tympanic membrane patch graft or bilayer graftdevice in which the central region includes ribs designed to match thenatural structure in the location of the perforation (FIG. 10C), andplacement of the device over the perforation to effect repair (FIG.10D).

Alternatives

While various arrangements of scaffolds and voids are described andshown herein, other arrangements are possible. Other examples ofarrangements can include ribs formed in true circle shapes, or irregularcircular shapes. In some other examples, the ribs of a scaffold mayconform to a different configuration. For example, a scaffold may beformed of generally straight ribs, some of which are offset by an angle(e.g., 45° or 90°) to form a regular pattern or mesh, e.g., oftriangular, square, parallelogram, hexagonal (see, e.g., FIGS. 3C-A and3C-B), or other shapes. In another example, the shape of each rib may becreated to reflect natural patterns, e.g., Brownian motion or fractalpatterns, to form an irregular mesh, or random patterns can be created.

As noted above, drugs, growth factors, and/or cellular adhesion andinvasion materials can be mixed with or added to the infill material orscaffold material or coated onto or soaked into the scaffold and/orinfill material. However, in some implementations, some or all of thesedrugs, growth factors, and/or cellular adhesion and invasion materialscan instead be applied to the exterior surfaces of the graft deviceseither before or after implantation. This may be desirable, for example,when using a mass produced graft without such an application, but wherea drug, growth factor, and/or cellular adhesion and invasion material isadded for a particular patient.

As described above, different processes of manufacture can be used tocreate the graft devices described herein. For example, instead offilling the voids of the scaffold by submerging the scaffold in theinfill fluid, the voids may be filled by 3D printing. For example, some3D printers allow for multiple print materials to be used in a singledevice. In such a printer, the scaffold could be printed with a firstmaterial, and a second material could be printed into the voids.Alternatively, the finished scaffold could be loaded into a different 3Dprinter that is instructed to print the infill material into thefinished scaffold's voids.

In some cases, the infill material may be the same material as used toform the scaffold. For example, after printing the scaffold, the same 3Dprinter may print the infill material in the voids. By doing so, themechanical properties of the scaffold may be preserved, even as theentire graft is printed of a single material.

EXAMPLES

The invention is further described in the following examples, which donot limit the scope of the invention described in the claims.

Example 1—Printing a Scaffold

This example covers the creation of a tympanic membrane graft scaffolddesigned based on a human tympanic membrane.

The ultrastructure of the human tympanic membrane was analyzed and acomputerized 3D model of the membrane's fibrous layer was created. Ribpattern, thickness, and 3D conical configurations served as designvariables for the printed scaffold.

A multilayered, artificial tympanic membrane graft scaffold wasfabricated using a 3D printer. The scaffold was printed withpolydimethylsiloxane (PDMS) ink in a pattern derived from theexamination of the human tympanic membrane, with a rib thickness of 120microns, an overall diameter of 12 millimeters, and a 3D conicalconfiguration. The scaffold, when printing was complete, was heat curedand removed from the substrate using forceps. Examples of printedtympanic membrane graft scaffolds are shown in FIGS. 2A to 2E.

FIG. 2A shows a top view of a graft device scaffold, with the centralregions filled with an infill material. FIG. 2B shows a graft devicewith a single ring design for attachment to the ossicular chain. FIG. 2Cshows a graft device with a single arch ring design for attachment tothe ossicular chain. FIG. 2D shows a graft device with a double archring design for attachment to the ossicular chain.

FIGS. 2E-A to 2E-D are photographic representations of tympanic membranepatch graft scaffolds that were designed and printed at a total diameterof 5 mm in two fiber configurations: 4 radial (R) and 4 arc (A) fibersand 6R and 6A fibers. Radial and circumferential fiber configurationswere chosen based on the desire to mimic the basic circumferential andradial fiber arrangement of the human tympanic membrane, to achieveconsistency among printing results, and to obtain the ability to easilymanipulate fiber arrangement. Using the same material, a thickerperipheral border region was also printed to stabilize the TM patchscaffold and allow appropriate positioning for cell studies. The borderregion consisted of one outer ring intersecting the outmost vertices ofthe inner square tympanic membrane graft patch scaffold, with linearfibers connecting the midpoint of each side of the scaffold to theborder ring.

These results demonstrate that a tympanic membrane graft can befabricated based on a 3D printed scaffold having voids to be filled withan infilled material.

Example 2—Infilling Voids of a Scaffold

This example covers the infilling of a tympanic membrane graft scaffoldwith an infill material to create a solid graft. An infill mixture oftype III collagen with fibrin 30% was prepared and placed into apipette. A printed tympanic membrane graft scaffold was placed into acircular well using forceps, as shown in FIG. 5A. Next, the infillmaterial was introduced into the voids of the scaffold, as shown in FIG.8D. The scaffold was allowed to rest in the collagen for twenty minutesat 37° Celsius. Using forceps, the graft was removed from the well andplaced in deionized water in a 37° Celsius incubator. FIG. 5B shows thegraft with the collagen filling the voids of the scaffold. These resultsdemonstrate that an infill material can be used to fill the voids of ascaffold and cured to create a tympanic membrane graft.

Example 3—In Vitro Cell Studies

This example covers experiments designed to determine if human neonataldermal fibroblasts will colonize and grow over non-absorbable (PDMS) orabsorbable (PLA) tympanic membrane grafts in vitro.

PDMS or PLA scaffolds were prepared as described in Example 1, and asshown in FIG. 11A-1 . Some were then coated with a fibrin/collageninfill mixture as described in Example 2, and the results are shown inFIG. 11A-2 . Scaffolds and infill, once cured and solidified, were thenplaced in cell culture dishes with neonatal dermal fibroblasts. GFP(green fluorescent protein) expressing human neonatal dermal fibroblasts(HNDFs) were seeded at 200,000 cells/well into 6-well plates and allowedtwenty four hours to adhere to the dish to form confluent layers. Duringthis time, the tympanic membrane grafts were submerged in mediaovernight in an incubator. The tympanic membrane grafts were laiddirectly on top of the confluent layer of HNDFs and held down with glassslide pieces to have contact with the HNDFs and to inhibit floating. Theglass pieces were removed after twenty four hours and imaging wasconducted after six days (144 hours).

FIGS. 11A-3 and 11A-4 show height maps showing the location of HNDFs inthe z-axis following 6 days adjacent to 200,000 HNDFs per well. Red(gray) represents HNDFs on the bottom of the well plate and green (lightgray) represents HNDFs at the top of the viewing plane. FIGS. 11B-1 and11B-2 are confocal microscope z-stack images that demonstrate cellulargrowth over PLA scaffolds with either fibrin infill alone orfibrin/collagen infill. FIGS. 11B-1 and 11B-2 present the same data thatis shown in FIG. 11A-4 from a different view, along the Y axis whileFIG. 11A-4 is shown along the Z axis.

These studies demonstrate that cells were able to grow on the surfacesscaffolds and infill materials. In addition, these studies demonstratethat the scaffold and infill materials (PDMS/PLA/Fibrin/Collagen) arenot toxic to fibroblasts and would allow cellular ingrowth and adhesionfollowing implantation. As a cellular toxicity study, we find these tobe reasonable materials for use as tympanic membrane implants.Particularly, this type of cell growth shows that there will be cellulargrowth over and into the graft from the middle ear and external auditorycanal, ensuring graft take.

Example 4—Acoustic and Mechanical Testing

Acoustic testing was designed to determine the acoustic properties ofnon-absorbable and absorbable grafts in relationship to temporalisfascia and normal tympanic membrane with an intact ossicular chain. Thehuman tympanic membrane fibrous layer was examined using electronmicroscopy and used as the basis for initial tympanic membrane design.Biocompatible absorbable and non-absorbable materials were printed asthin sheets and patterned tympanic membrane scaffolds. Scaffolds werelayered with fibrin/collagen infill to create an impermeable membrane asdescribed in Examples 1 and 2 above. In particular, scaffolds of varyingdiameters (8-12 mm), thicknesses (50-200 microns), and radial ribarrangements (4-32 ribs) were successfully printed and layered withsemi-translucent collagen/fibrin infill.

Acoustic properties of printed tympanic membranes were then determinedby digital opto-electronic holography and compared to fresh humancadaveric temporalis fascia and human cadaveric tympanic membranes withintact ossicular chains. Printed and infilled tympanic membranes weremounted in artificial external auditory canal holders replicating theenvironment of the external auditory canal at 9 mm in diameter and 25 mmin length. Grafts can be coated with titanium dioxide to improvereflectance of the surface of the material. Mounted grafts weresubjected to total sound pressures of brief duration (tone pips) at 5different frequencies appreciated by humans and regularly tested duringaudiograms: from 0.5-15 kHz. Sound pressure amplitudes ranged from80-110 dB SPL and pulse width of 50-100 μs. Sound stimuli are generatedby broadband sound sources driven by a power amplifier through the longend of the artificial external auditory canals.

Digital Opto-Electronic Holography (DOEH) provides real-time-averagedholograms of membrane motion, providing qualitative and quantitativefull-field information on the sound induced motion of TM grafts. FIGS.12A-A to 12A-G show images of examples of different graft testingholders. FIGS. 12A-A to 12A-D are computer-generated images of a lid (A)and base (B) of one version of a graft holder that uses a piston designto keep the tympanic membrane graft in place. The holder included a wellfor secure placement of a single TM composite graft or temporalisfascia. The cap was designed to completely cover the border region suchthat only the scaffold and collagen/fibrin infill were subject toacoustic testing. Examples of dimensions for the base can be: inner holediameter of 9 mm, well diameter of 25.5 mm, outer diameter of 35 mm,inner well depth of 3 mm, and total length of 30 mm. The cap can havethe same inner and outer radii as the base with an extruded portiondiameter of 25 mm, extruded portion length of 2.5 mm, and total lengthof 5.5 mm. Images in FIGS. 12A-C and 12A-D show the lid and holder ofanother version of the tympanic membrane graft holder that uses asliding mechanism to secure the tympanic membrane graft for testing.FIG. 12A-E is a photo that shows actual fabrications of the computerimages of FIGS. 12A-A to 12A-D. FIG. 12A-F shows a 3D printed tympanicmembrane graft inside of the testing device shown in FIGS. 12A-C/D. FIG.12A-G shows the graft holder when closed. These holders are used in aholography and mechanical impedance testing system.

Mounted grafts were subjected to DOEH to assess magnitude and phaseangle of motion following acoustic stimulation. Both modal responses touniform stimulation, as well as traveling wave-dominated motions of the3D printed tympanic membrane were recorded. To determine the appropriatethickness of a 3D printed tympanic graft, preliminary experiments wereconducted to understand how materials and thicknesses affectdisplacement in response to acoustic energy. A host of materials andthicknesses were tested and representative images are shown. FIGS. 12B-1to 12B-4 demonstrate similar displacement magnitudes of 3D printedsheets of PDMS or PLA compared to human tympanic membrane attached toossicular chain and human temporalis fascia, which is a currently usedtympanic membrane graft material during tympanoplasty. FIG. 12B-1demonstrates normal displacement magnitude of tympanic membrane attachedto an ossicular chain in a human cadaveric temporal bone. Maximumdisplacement of human TM in temporal bone model was around 0.25micrometers.

Three comparison groups are shown: human temporalis fascia shown in FIG.12B-2 , PDMS (100 microns thick) shown in FIG. 12B-3 , and FlexEco™ PLA(200 microns thick) shown in FIG. 12B-4 . These comparison datademonstrate similar displacement magnitudes. Slight increases indisplacement of human temporalis fascia, PDMS, and PLA as compared tohuman cadaveric tympanic membrane in a temporal bone may be due to anabsence of a dampening effect from the lack of an intact ossicular chainin the models. The bottom row of figures (FIGS. 12B-5 to 12B-8 )demonstrate the different phase of the tympanic membrane in response tosound. FIG. 12B-5 demonstrates a uniform pattern of tympanic membranewhich is connected to the ossicular chain. FIGS. 12B-6 to 12B-8demonstrate that FlexEco PLA (12B-8) and PDMS devices (12B-7) both showsimilar phase distributions compared to human TM (12B-5), but varyslightly compared to devices made of temporalis fascia (12B-6).

A representative comparison of acoustic properties of 3D printedtympanic membrane graft influenced by fiber arrangement was performedusing digital opto-electronic holography after response to a 522 Hz puretone sound. FIG. 12C, the top row shows the 3D printed rib structure ofSE1700 PDMS in two configurations, one with 32 circular (C) ribs and 32radial ribs (R) (FIG. 12C-1A) and one with 16C ribs and 8R ribs (FIG.12C-2A) on a BYTAC Teflon™ printing surface. The second row shows thesesame scaffolds infilled with a collagen/fibrin mixture (FIGS. 12C-1B and12C-2B). The third row demonstrates magnitude of displacement of thesesame PDMS scaffolds (FIGS. 12C-1C and 12C-2C). Note similar displacementmagnitudes demonstrating that rib motion, differs based on scaffold ribarrangement. FIGS. 12C-1D and 12C-2D show clear differences in phasesbased on rib count and arrangement. This implies a “tunability” of TMgrafts based on rib count and arrangement.

A representative comparison of human TM and attached ossicular chain to3D printed tympanic membrane graft with 32 circular ribs and 32 radialribs to high frequency pure tone sound was performed. FIGS. 12D-1A and12D-2A show the magnitude of displacement of a human TM and ossicularchain compared to a PDMS scaffold with 32 circular scaffold ribs and 32radial ribs, respectively (note similarities in magnitude ofdisplacement, as well as complex waves). FIGS. 12D-1B and 12D-2B showthe complicated phase patterns of both human TM with ossicular chain aswell as a 3D printed tympanic membrane, respectively.

Digital Opto-Electronic Holography results were compared to acquireddata on the native human tympanic membrane. Within 3D printed materials,a relationship between specific acoustic properties (magnitude and phaseangle) and structure (rib size and orientation) was determined. Optimalacoustic properties were defined as those of a normal healthy humantympanic membrane.

Printed sheets and scaffolds with infill showed frequency dependentvariations in motion patterns (number and location of peaks) at 1000,4000, and 8000 Hz. The motion patterns were affected by the materialsused to prepare the sheets and also were affected by the rib patterns ofthe scaffolds. Certain materials and designs of tympanic membranescaffolds showed similar motion patterns to human tympanic membrane andfascia. The normalized displacement magnitude (micrometers/Pa) of sheetsand scaffold and infill were similar to displacement of fascia andtympanic membranes.

Additional testing for the 3D printing tympanic membrane grafts includesmechanical testing, which included determination of distensibility tonegative and positive pressures. The pressure of the middle ear rangesfrom +50 to −200 d Pa. In chronic Eustachian tube dysfunction (ETD),there may be continued negative pressure in the middle ear. Using atympanic membrane holder in a sealed vacuum chamber, the 3D tympanicmembrane graft is exposed to negative or positive pressure at a varietyof physiologic and/or supra-physiologic values for several time points,such as one day, one week, and one month. The tympanic membrane graftsare then examined by microscopy to determine any change in overall shapeand ultrastructure. Human temporalis fascia undergoes similar testingand serves as a control. Additional acoustic experiments includeacoustic testing after negative or positive pressure and mechanicaldeformation to determine if there are any changes to acoustic propertiesand ultrastructure.

Additional testing for the 3D printing tympanic membrane graft includedlaser Doppler vibrometry (“LDV”) measurements for tympanic membranegrafts of various materials. FIGS. 15A-D show velocity normalized bystimulus sound pressure of tympanic membrane composite grafts, fascia,and the human TM across the human frequency range. FIG. 15A shows thegraphical results of comparison testing of all tested materials in whichmeasured mean velocity for three specimens of 8C/8R TM composite graftsof varying composition (PDMS, PLA, and PCL), fascia, and human TMs withintact middle ears. FIGS. 15B-D show the graphical results forcomparisons of grafts of different materials (PDMS, PLA, and PCL,respectively) with different designs (8C/8R and 16C/16R). Grafts ofhigher fiber count showed slightly lower mean velocities.

The results of these acoustic tests indicated that the materials andprinting dimensions are useful as artificial tympanic membrane scaffoldsand indicate they can be acoustically tuned. In addition, these testsconfirm that the tympanic membrane graft devices and the bilayer graftdevices can be acoustically tuned by, for example, changing the radialand circular rib arrangement, other geometric parameters, materials,etc. Sound-induced motion patterns of grafts that mirror the motionpatterns of the tympanic membrane were determined and analyzed to alterthe number of fibers/ribs and material type.

Example 5—Animal Studies—Guinea Pigs, Sheep, and Chinchillas

Guinea pig, sheep, and chinchilla models were used for ototoxicity andhearing tests. The guinea pig is a useful animal model for ototoxicityand hearing studies because the middle ear space is readily accessibleand one can perform auditory brainstem responses (ABR) to determinehearing thresholds. Sheep are useful models for tympanic membrane graftstudies. The chinchilla model is useful for ototoxicity testing andbaseline ABR testing as well as distortion product otoacoustic emissions(DPOE) testing.

FIG. 13A shows a sheep model tympanic membrane with a perforation made.FIG. 13B shows a trimmed tympanic membrane graft in a sheep model. Size,accessibility, and the middle ear environment are generally reflectiveof the human ear. Sheep have been used for middle ear surgical trainingas well as for drug and device testing in otologic surgery. In addition,the tympanic membrane graft devices described herein are placed incadaveric human tympanic membranes.

Ototoxicity studies were performed by using both physiology andhistological experiments. For physiology experiments, animals undergobaseline auditory brainstem response (ABR) testing to determine baselinehearing threshold. Next a post-auricular incision is made, and themiddle ear space is entered through the bulla. Following entry of themiddle ear space, a host of different types of graft materials (asdescribed above) are placed adjacent to the round window. The opening ofthe middle ear space is then covered with soft tissue, such as muscleand/or facia, the incision is sutured, and the animal allowed torecover. The animal then undergoes testing of hearing thresholds via ABRat 1 week, 2 weeks, 3 weeks, 1 month, 2 months, 3 months, up to 1 yearor any permutation. Results suggest no ototoxic features of utilizedmaterials (PDMS, PLA, PCL, collagen, fibrin, and hydrogel).

For histology experiments, the animals are perfused with saline and thenparaformaldehyde. The middle ear and inner ear structures are thensectioned and histologically analyzed. Sections are reviewed forevidence of inflammation, calcium deposition, as well as markers of haircell loss and neuronal loss in the cochlea. A variety ofimmunohistological stains are used for this purpose. In addition, the 3Dprinted material placed in the middle ear space is also examined bylight, fluorescence, and/or electron microscopy to understand any signsof inflammation, degradation, or other changes.

For graft repair experiments in the sheep large animal model, animalsare appropriately anesthetized. An incision is made in the tympanicmembrane. The graft is then sized appropriately and placed over or underthe defect, similar to human surgery. The animals are allowed torecover. The contralateral ear or another animal with a similar defectmade in the tympanic membrane but without the graft is used as acontrol. After every month up to 12 months, the animals are assessed forgraft take, healing of the tympanic membrane and to determine any signsof infection, inflammation, shifting of graft materials or other notablechanges. After similar time points, animals have the tympanic membranegraft with surrounding structures removed and analyzed histologically.The graft materials are examined by light, fluorescence, and/or electronmicroscopy to understand any signs of inflammation, degradation, orother changes.

FIGS. 14A to 14C show the use of a tympanic membrane graft “patch” asdescribed herein to seal a perforation of a tympanic membrane in thechinchilla small animal model. The ototoxic potential of three specific3D printed tympanic membrane composite grafts was tested by surgicallyimplanting them within the chinchilla middle ear space. These graftdevices were made of PDMS, PLA and PCL and 3D printed as describedherein. The grafts scaffolds were then infilled with a bovine fibrinhydrogel. Anesthetized animals underwent baseline auditory brainstemresponse (ABR) and distortion product otoacoustic emissions (DPOE)measurements.

Under sterile conditions, the 3 mm TM grafts were placed through thebulla between the tympanic surface of the TM and the round window niche.As a control operation, the contralateral bulla was entered but no graftwas placed. Physiologic responses to the surgery and graft implantationare assessed via ABR and DPOE at 3 or 6 months. The graft and inner earof the chinchilla will be then be analyzed for inflammatory mediatorsusing standard otopathology techniques and compared to the control ear.Immunohistochemical techniques will also be used to evaluatemacrophage/monocyte markers such as IBA1, CD68, CD163, as well as CD45.

Chinchillas are a well-established inner and middle ear animal model andare commonly used for auditory research.

Based on preliminary animal tests, it appears that biomimetic graftsdescribed herein, including the bilayer design, are not cochleotoxic. Incadaveric models they can be used to effectively repair a perforatedtympanic membrane perforation.

Example 6—Tympanic Membrane Patch Graphs Having Conical Shapes

FIG. 16A-C are photographic representations of tympanic membrane patchgraphs having conical shapes. FIG. 16A shows a conical shaped tympanicmembrane graft with a central height of 2 mm. FIG. 16B shows a tympanicmembrane graft scaffold of 8C/8R with a central height of 3 mm. FIG. 16Cshows tympanic membrane grafts of varied heights.

Unlike fascia, which does not possess the fibrous scaffold architectureor conical shape of a human tympanic membrane, a 3D printed tympanicmembrane graft may be created as described herein. Such a conicaltympanic membrane graft may receive and transmit sound-induced motionpatterns that are dependent upon the graft's conical depth.

Grafts were printed upon 3D molds of 9 mm diameter of varied conicalheights (0 mm, 1 mm, 2 mm, and 3 mm). Direct ink writing was used toextrude PDMS through a 410 μm nozzles under ambient conditions infilamentary form to create solid sheets and scaffolds of 200 μmthickness. Tympanic membrane grafts of 8C/8R were infilled with an 80mg/mL bovine fibrin hydrogel and stored in deionized water at 37° C.

To perform finite-element analysis (FEA), 3D geometry and mesh of 3Dprinted membranes were created. The geometries were discretized using 3Dquadratic tetrahedral elements. Degrees of freedom were fixed where themembrane covered the holder surface in our experimental setup.Sinusoidal pressure was applied to the 9 mm membrane surfacecorresponding to the central cylindrical opening of the graft holder.The Young's modulus was considered to be 4.1 MPa and the damping ratiowas considered to linearly increase from 0.056 at 200 Hz to 0.071 at6300 Hz. Both material parameters were calculated based on laser Dopplervibrometry measurements using a mixed analytical-experimental methoddeveloped in our laboratory.

To perform digital opto-electronic holography (DOEH), an interferometerwas used to record motion-induced holograms in real-time through twointerfering laser beams, providing qualitative and quantitativefull-field information of the sound induced motion of a membrane. Themagnitude and phase angle of displacement of more than 400,000 points onthe surface of a membrane were acquired simultaneously. A membrane wasmounted in a holder with an integrated sound coupler, placed in front ofthe interferometer camera head, and oriented such that the surface ofthe membrane is perpendicular to the object beam of the laser. Themembrane was held in the holder by a combination of viscous forces andnegative pressure restricted to the membrane support. Pure tones (0.1,1, 3 and 6 kHz) were played from the sound source and the displacementwaveform for each point on the membrane surface is recorded instroboscopic mode. Fourier transformations were used to computedisplacement magnitude and phase at each point.

Cones of varying depth show frequency dependent surface motion patternsmeasured by DOEH. Surface motion patterns are progressive, from simple(<1000 Hz) to complex (3000 Hz), to highly ordered (6000 Hz). Absolutedisplacement magnitude value and patterns vary by cone height. Flatmembranes tend to have larger motion than 1, 2, or 3 mm cones by afactor of 5˜10 below 1000 Hz, while the differences become smaller athigher frequencies.

Finite element analysis (FEA) was predictive of surface motion patternsin response to sound. Differences in motion patterns and displacementamplitude by conical depth were predicted using FEA. Irregularities inprinted grafts explain asymmetries in measured patterns. Nodes ofmaximal displacement appear asymmetrically in DOEH results and becomemore pronounced at greater conical depths. Irregularities in themanufacturing process of grafts leave a seam along solid membranegrafts, producing asymmetric motion. Infilled TM graft scaffoldsdemonstrate similar displacement to solid sheets. At low frequencies,surface motion patterns of PDMS 2 mm conical scaffolds, infilled withcollagen/fibrin hydrogel, show simple, nodal patterns.

The results show that uncoupled human TMs have similar displacementpatterns as the 3D graft devices described herein. The isolated TM (inannulus but without middle ear load) has measured displacement patternsthat show some similarities to 2 mm solid cones and 2 mm in-filled graftscaffolds. However, in-filled grafts and conical membranes move somewhatless than the human TM.

Laser Doppler vibrometry (“LDV”) results show that increasing conicaldepth results in higher stiffness at low frequencies. LDV measuredvelocity at the center point of printed grafts consistently demonstratesan inverse relationship between graft height and motion. This suggeststhat conical shape independently leads to increased stiffness of themembrane. Measured first resonant frequencies by flat and conical graftsdemonstrate a progressive shift to higher frequencies for cones ofgreater depth. Velocity differences at high frequencies are lessobvious. When comparing conical grafts of different heights, consistentdifferences are less apparent above 1000 Hz.

Other Embodiments

It is to be understood that while the invention has been described inconjunction with the detailed description thereof, the foregoingdescription is intended to illustrate and not limit the scope of theinvention, which is defined by the scope of the appended claims. Otheraspects, advantages, and modifications are within the scope of thefollowing claims.

What is claimed is:
 1. An artificial tympanic membrane device,comprising: a scaffold comprising a plurality of ribs comprising a firstmaterial, the plurality of ribs including a first plurality of ribs anda second plurality of ribs, the first plurality of ribs comprisingcircumferential ribs having a concentric arrangement and the secondplurality of ribs comprising radial ribs forming a radial pattern; and aplurality of spaces between the radial ribs forming the radial pattern,wherein the scaffold is dimensioned and configured to repair or replacea damaged or missing tympanic membrane.
 2. The device of claim 1,wherein the plurality of ribs are formed in a hub and spoke arrangement.3. The device of claim 1, wherein the artificial tympanic membrane formsa circular 3-dimensional cone shape.
 4. The device of claim 1, whereinthe first material comprises one or more materials selected from thegroup consisting of: polydimethylsiloxane (PDMS), hyaluronic acid (HA),poly(glycolic acid) (PGA), poly (lactic-co-glycolic acid) (PLGA),polylactic acid (PLA), polyester carbonate urethane urea (PECUU), polyoctamethylene maleate anhydride citrate (POMaC), poly(glycerol sebacate)(PGS), poly(octanediol-co-citrate) (POC), polyurethane, collagen,fibrin, extracellular matrix, nylon, silk, poliglecaprone, and elastin.5. The device of claim 1, further comprising a second materialcomprising one or more materials selected from the group consisting of:collagen, extracellular matrix, hydrogels, titanium dioxide, cellulose,gelatin, agarose, alginate, poly(N-isopropylacrylamide), hyaluronicacid, poly(vinyl alcohol) (PVA), poly (acrylic acid) (PAA),polycaprolactone, poly(3-hydroxybuterate-co-3-hydroxyvalerate, pluronicPLA, PGA, transglutaminase, PLGA, PDMS, poliglecaprone, polyestercarbonate urethane urea (PECUU), poly octamethylene maleate anhydridecitrate (POMaC), poly(glycerol sebacate) (PGS),poly(octanediol-co-citrate) (POC), polyurethane, and a mixture ofcollagen and fibrin.
 6. The device of claim 1, further comprising acellular adhesion-inducing material, a cellular invasion-inducingmaterial, small molecules, biologics, growth factors, a drug, a drugeluting material, or any combination thereof.
 7. The device of claim 6,wherein the growth factor comprises one or more of a fibroblast growthfactor (FGF), vascular endothelial growth factor (VEGF),platelet-derived growth factor (PDGF), and a keratinocyte growth factor(KGF).
 8. The device of claim 1, further comprising living cells,wherein the scaffold is used as a substrate for the living cells.
 9. Thedevice of claim 8, wherein the living cells are selected from the groupconsisting of fibroblasts, chondrocytes, keratinocytes, stem cells,progenitor cells, and epithelial cells.
 10. The device of claim 1,wherein the device has a diameter based on a diameter of a naturaltympanic membrane, or a perforation or defect in a natural tympanicmembrane of a specific patient.
 11. The device of claim 10, wherein thenatural tympanic membrane is a human tympanic membrane, and wherein thedevice has a thickness of about 10 microns to about 800 microns, adiameter of about 0.5 millimeters to about 19 millimeters, or both. 12.The device of claim 1, wherein the device is impermeable to air orliquids.
 13. The device of claim 1, wherein the device is permeable toair and permeable to any one or more of small molecules, biologics,steroids, and antibiotics.
 14. The device of claim 1, further comprisingon one surface of the tympanic membrane graft an ossicular connectorformed as an artificial umbo and takes the shape of a natural umbo, aring, a loop, a hinge, or a ball and socket.
 15. A method of implantingthe device of claim 1 into a patient to repair or augment a tympanicmembrane or to replace a missing tympanic membrane or missing portionthereof, the method comprising: accessing a tympanic membrane or alocation of a missing tympanic membrane or missing portion thereof;obtaining an appropriately sized and configured artificial tympanicmembrane device; and securing the artificial tympanic membrane device torepair or augment the tympanic membrane or to replace the missingtympanic membrane or missing portion thereof.
 16. The method of claim15, wherein the method is performed in a clinical setting with orwithout local analgesia, but without sedation or general anesthesia. 17.The method of claim 15, wherein the method provides improved orreconstructed hearing.
 18. A method of fabricating the device of claim1, the method comprising: forming the scaffold comprising the pluralityof ribs using the first material, wherein the scaffold is approximatelyflat or has a shallow cone shape.
 19. The method of claim 18, whereinforming the scaffold comprises printing the scaffold with athree-dimensional (3D) printer onto a substrate.
 20. The method of claim19, wherein the scaffold comprises one or more of glass, poloxamer,polytetrafluoroethylene (PTFE), and metal foil.
 21. A bilayer tympanicmembrane device comprising a pair of artificial tympanic membranedevices of claim 1, wherein a first of the pair of artificial tympanicmembrane devices further comprises a projection, and wherein a second ofthe pair of artificial tympanic membrane devices further comprises anopening configured to enable insertion of the projection, wherein thefirst and the second tympanic membrane devices are secured to each otherto form the bilayer tympanic membrane device, wherein the projection andopening are dimensioned and configured to permit a tympanic membrane tobe sandwiched between the two artificial tympanic membrane devices. 22.The bilayer tympanic membrane device of claim 21, wherein the openingand the projection comprise a lock and key configuration, a socket andball configuration, or an opening and hinge configuration.
 23. Theartificial tympanic membrane device of claim 1, wherein a solid membranefills the spaces between the radial ribs, the solid membrane comprisingthe first material or a second material.
 24. The artificial tympanicmembrane device of claim 1, wherein each of the circumferential ribs isin contact with one or more adjacent circumferential ribs, the scaffoldthereby including no spaces between the circumferential ribs.